Tissue resecting system

ABSTRACT

A surgical system includes a first instrument defining a first channel and a second instrument receivable by the first channel. The second instrument defines a second channel. A valve coupled to the first instrument controls fluid flow through the first channel, such that impedance of fluid flow through the first channel is substantially the same without the second instrument received in the first channel and with the first channel partially blocked by the second instrument. In another aspect, a surgical apparatus includes an outer member and an inner member received within the outer member to define a first channel therebetween. The inner member houses an optical lens and defines a second channel for receiving a surgical instrument. The first and second channels are configured such that a pump having an inflow rate of up to about 0.7 L/min connected to the second channel can maintain fluid pressure inside an organ.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a division of prior application Ser. No. 14/473,389,filed Aug. 29, 2014, now allowed, which is a continuation of priorapplication Ser. No. 13/860,654, filed Apr. 11, 2013, now U.S. Pat. No.8,852,085, which is a continuation of prior application Ser. No.13/212,240, filed Aug. 18, 2011, now U.S. Pat. No. 8,419,626, which is acontinuation of prior application Ser. No. 10/927,244, filed Aug. 27,2004, now U.S. Pat. No. 8,062,214, each of which is hereby incorporatedby reference herein in its entirety.

TECHNICAL FIELD

This invention relates to a tissue resecting system.

BACKGROUND

Endoscopic surgery of a distensible organ, such as a uterus, may beperformed with an endoscope that is insertable into the uterus and aresector that passes through the endoscope to cut or otherwise treattissue in the uterus. During surgery, it often is desirable to distendthe uterus with a fluid, such as saline, sorbitol, or glycine, in orderprovide a visible working space. Fluid can be infused into the uterusand removed from the uterus through the endoscope and/or resector.

SUMMARY

If the outflow of fluid from the uterus is greater than the inflow offluid to the uterus, the uterus may collapse back to its normal state,making visualization of the uterus difficult. On the other hand, if theinflow of fluid is greater than the outflow of fluid such that thepressure created by the fluid is greater than the patient's meanarterial pressure, excess fluid can enter the patient's vascular system(known as intravasation), which can lead to serious complications ordeath.

To aid in addressing these issues, in an aspect of the invention, asurgical system includes a first instrument defining a fluid flowchannel and a second instrument receivable by the first instrument fluidflow channel. The second instrument defines a channel. The systemincludes a valve coupled to the first instrument and configured tocontrol fluid flow through the first instrument channel. The valve isconfigured such that impedance of fluid flow through the firstinstrument channel is substantially the same without the secondinstrument received in the first instrument channel and with the firstinstrument channel partially blocked by the second instrument such thatthe first instrument channel is limited to a region between the firstand second instruments.

Embodiments of this aspect of the invention may include one or more ofthe following features.

For example, the first instrument includes an outer member and an innermember. The inner member defines the first instrument channeltherethrough. The inner member is received within the outer member, andthe outer member and the inner member define a second fluid flow channeltherebetween. The second instrument includes a tube defining the secondinstrument channel therethrough. The tube partially blocks the firstinstrument fluid flow channel when received therein. The second fluidflow channel has a cross-sectional area of, e.g., about 0.0083 to about0.0249 square inches, preferably about 0.0166 square inches. The firstinstrument fluid flow channel has a cross-sectional area of, e.g., about0.0053 to about 0.0159 square inches, preferably about 0.0106 squareinches. The second instrument channel has a cross-sectional area of,e.g., about 0.0042 to about 0.013 square inches, preferably about 0.0085square inches.

In an illustrated embodiment, the valve includes a housing and a bodywithin the housing. The body defines an opening therein and is moveablerelative to the housing between a first position in which the openingand the first instrument channel define a first fluid flow path having afirst impedance and a second position in which the opening is arrangedto receive the second instrument therethrough such that the opening andthe first instrument channel define a second fluid flow path that has asecond impedance substantially equal to the first impedance.

The system as illustrated includes a pump and the first instrument isconfigured to connect to the pump such that the pump infuses fluidthrough the first instrument channel. The pump is programmed to infusefluid through the first instrument channel to maintain a substantiallyconstant pressure of between about 60 mm Hg and about 120 mm Hg inside adistensible organ. A sensor coupled to the pump senses a flow impedanceat a given flow rate, and a controller coupled to the sensor and thepump compares the flow impedance to a predetermined flow impedance forthe given flow rate to verify the identity of the first and secondinstruments.

The second instrument channel is in fluid communication with a source ofsuction and a regulator is interposed between the second instrumentchannel and the source of suction to regulate an amount of suctionapplied through the second instrument channel.

According to another aspect of the invention, a surgical system includesa first instrument defining a fluid flow channel, and a secondinstrument receivable by the first instrument fluid flow channel. Thesecond instrument defines a channel. The system includes a means formaintaining a substantially constant impedance of fluid flow through thefirst instrument channel with and without the second instrument receivedin the first instrument channel.

According to another aspect of the invention, a method includes: (a)positioning a valve coupled to a first instrument in a first position;(b) introducing fluid to a distensible organ through the valve with thevalve in the first position and through a channel in the firstinstrument; (c) positioning the valve in a second position; (d)introducing a second instrument through the valve with the valve in thesecond position and through the first instrument channel; and (e)introducing fluid to the distensible organ through the valve with thevalve in the second position and through a region of the firstinstrument channel located between the first and second instruments. Theimpedance of fluid flow in steps (b) and (e) is substantially the same.

Embodiments of this aspect may include one or more of the followingfeatures. The method includes maintaining substantially constant fluidpressure within the distensible organ with and without the secondinstrument received in the first instrument channel. Maintainingincludes suctioning fluid from the distensible organ through the secondinstrument. The method includes regulating a pump coupled to the valvefor introducing fluid through the valve.

According to another aspect of the invention, a valve includes a housingand a body within the housing. The body defines an opening therein. Thebody is moveable relative to the housing between a first position inwhich the opening and the housing define a first fluid flow path havinga first impedance and a second position in which the opening is arrangedto receive a surgical instrument therein. The opening is configured suchthat with the surgical instrument received therein, the opening and thehousing define a second fluid flow path that has a second impedancesubstantially equal to the first impedance.

Embodiments of this aspect may include one or more of the followingfeatures. The opening includes a throughbore through the body forreceiving the surgical instrument. The opening includes a second borehaving a first open end and a second closed end in the body. The secondbore is arranged substantially orthogonal to the throughbore andintersects the throughbore. The housing defines an inlet and an outlet.When the body is in the first position, the throughbore is partiallyaligned with the inlet and the first fluid flow path is from the inlet,through the throughbore, and then through the second bore to the outlet.When the body is in the second position, the second bore is aligned withthe inlet and the second fluid flow path is from the inlet, through thesecond bore, and then through the throughbore to the outlet.

According to another aspect of the invention, a method of regulatinginflow through a valve includes positioning the valve in a firstposition wherein the valve has a first impedance; positioning the valvein a second position; and introducing a surgical instrument through thevalve in the second position. A combination of the surgical instrumentand the valve has a second impedance substantially equal to the firstimpedance.

According to another aspect of the invention, an apparatus for surgeryincludes an outer member and an inner member received within the outermember. The outer member and the inner member define a first channeltherebetween. The inner member houses an optical lens and defines asecond channel for receiving a surgical instrument. The first and secondchannels are configured such that a pump having an inflow rate of up toabout 0.7 L/min connected to the second channel can maintain fluidpressure inside an organ.

Embodiments of this aspect may include one or more of the followingfeatures. A pump is coupled to the second channel to introduce fluidthrough the second channel at an inflow rate up to about 0.7 L/min. Theouter member defines a plurality of holes in fluid communication withthe first channel. The plurality of holes is positioned in a distalportion of the outer member. The second channel has a D-shapedcross-section. The first channel has a cross-sectional area, e.g., ofabout 0.0083 to about 0.0249 square inches, preferably about 0.0166square inches. The second channel has a cross-sectional area of, e.g.,about 0.0053 to about 0.0159 square inches, preferably about 0.0106square inches. The second channel receives the surgical instrument. Thesurgical instrument has a suction channel with a cross-sectional areaof, e.g., about 0.0042 to about 0.013 square inches, preferably about0.0085 square inches. A valve is coupled to the inner member forregulating inflow through the second channel such that the valve and thesecond channel have a first impedance equal to a second impedance whenthe surgical instrument is received in the second channel.

According to another aspect of the invention, a fluid management systemincludes a pump configured for coupling to an endoscope to infuse fluidthrough the endoscope at a given flow rate. A sensor is coupled to thepump that senses a flow impedance through the endoscope at the givenflow rate. A controller is coupled to the sensor and programmed tocompare the flow impedance to a predetermined flow impedance for thegiven flow rate to verify the identity of the endoscope and a surgicalinstrument received therein.

Embodiments of this aspect may include one or more of the followingfeatures. The sensor includes a pressure transducer. A circuit iscoupled to the controller and the pump for disabling the pump if theidentity of the surgical instrument and endoscope is not verified. Thecontroller is programmed to compare flow impedances to predeterminedflow impedances at multiple flow rates.

According to another aspect of the invention, a fluid management systemincludes means for infusing fluid through an endoscope at a flow rate,means for measuring a flow impedance through the endoscope at the flowrate, and means for comparing the flow impedance to a predetermined flowimpedance to verify the identity of the endoscope and a surgicalinstrument received therein.

According to another aspect of the invention, a method includesprogramming a pump with data on a predetermined flow impedance for anendoscope and surgical instrument assembly for a given flow rate,activating the pump to infuse fluid through the endoscope and surgicalinstrument assembly at the given flow rate, sensing a flow impedancethrough the assembly, and comparing the sensed flow impedance to thepredetermined flow impedance. The method may further include disablingthe pump if the flow impedance is not within a threshold value of thepredetermined flow impedance.

According to another aspect of the invention, a method includes infusingfluid into a distensible organ, and maintaining a substantially constantfluid pressure inside the distensible organ between about 60 mm Hg andabout 120 mm Hg.

According to another aspect of the invention, a system includes anendoscope defining a channel therethrough and a surgical instrumentreceived within the endoscope channel. The surgical instrument defines achannel therein for connection with a source of suction. A regulator iscoupled to the surgical instrument channel between the instrumentchannel and the source of suction to regulate an amount of suctionapplied through the instrument channel.

The details of one or more embodiments of the invention are set forth inthe accompanying drawings and the description below. Other features,objects, and advantages of the invention will be apparent from thedescription and drawings, and from the claims.

DESCRIPTION OF DRAWINGS

FIG. 1 is a schematic diagram of a resection system.

FIG. 2A is an exploded, perspective view of a hysteroscope of the systemof FIG. 1.

FIG. 2B is a perspective view of the assembled hysteroscope of FIG. 2A.

FIG. 3A is a longitudinal cross-sectional view of the hysteroscope ofFIG. 2B.

FIG. 3B is a cross-sectional view of the hysteroscope of FIG. 2B takenalong line 3B-3B.

FIG. 4 is a perspective view of the hysteroscope of FIG. 2B with aresector received therethrough.

FIG. 5 is a cross-sectional view of the hysteroscope and resector ofFIG. 4 taken along line 5-5.

FIG. 6A is a perspective cut-away view of primary and secondary valvesof the hysteroscope of FIG. 2B, with the primary valve in an openposition and the secondary valve in a first position.

FIG. 6B is a cross-sectional view of the primary and secondary valves asshown in FIG. 6A taken along line 6B-6B.

FIG. 7A is a perspective cut-away view of the primary and secondaryvalves of the hysteroscope of FIG. 2B, with the primary valve in an openposition and the secondary valve in a second position for receiving theresector.

FIG. 7B is a cross-sectional view of the primary and secondary valves asshown in FIG. 7A taken along line 7B-7B.

FIG. 8A is a perspective cut-away view of the primary and secondaryvalves of the hysteroscope of FIG. 2B, with the primary valve closed andthe secondary valve in the second position.

FIG. 8B is a cross-sectional view of the primary and secondary valves asshown in FIG. 8A taken along line 8B-8B.

FIG. 9 is a schematic diagram of a fluid management system of theresection system of FIG. 1.

FIG. 10 is a perspective view of an obturator for use with a sheath ofthe hysteroscope of FIG. 2A.

FIGS. 11-13 show the obturator, hysteroscope and resector in use.

FIG. 14 is a graph showing the impedance through the hysteroscope atvarious flow rates.

DETAILED DESCRIPTION

Referring to FIG. 1, a tissue resecting system 10 includes an endoscope,e.g., hysteroscope 100, having a distal portion 102 insertable into adistensible organ, e.g., a uterus, of a patient 20 to flow fluid intoand remove fluid from the organ. System 10 includes a cart carryingfluid bags 17 that are connected to hysteroscope 100 by an inflow line30 to deliver fluid to hysteroscope 100. Inflow line 30 runs through apump, e.g., peristaltic pump 310, of a fluid management control unit 300on cart 15. Pump 310 controls the pressure of the fluid delivered alonginflow line 30 to hysteroscope 100. System 10 also includes a gravitycontainer 40 on cart 15 connected by an outflow line 32 to an outflowvalve 105 on hysteroscope 100 to collect the outflow of fluid fromhysteroscope 100, under the force of gravity. In addition, system 10includes a surgical drape 22 connected by outflow line 32 to gravitycontainer 40 to collect fluid from patient 20.

System 10 further includes a resector 200 that is received withinhysteroscope 100 during use to resect tissue from the organ. Resector200 includes a handle 205 and a distal portion 210 that extends out ofdistal portion 102 of hysteroscope 100. Distal portion 210 includes aworking end 220, e.g., a morcellator, that can be actuated to cut tissuefrom the organ. Handle 205 includes a motor (not shown) coupled toworking end 220 to rotate working end 220 about a longitudinal axis tocut tissue. Also located on cart 15 is a resector control unit 60 ofsystem 10 connected by a wire 201 to resector 200 to control movement ofworking end 220. System 10 also includes a footpedal 62 connected tocontrol unit 60 by a wire 64 to actuate control unit 60.

Also located on cart 15 are four vacuum containers 42 of system 10connected by suction line 34 to a suction port 230 on resector 200 tocollect fluid and tissue suctioned through resector 200. At least one ofvacuum containers 42 includes a tissue trap 43 that collects tissuesuctioned through suction lines 34 for later examination, e.g., by apathologist. System 10 also includes a vacuum regulator 400 connected bya suction line 36 to vacuum containers 42 and by vacuum line 38 to avacuum source (not shown) to regulate suction provided by the vacuumsource through suction channel 204 of resector 200.

Also located on cart 15 is a fluid monitoring unit 18 of system 10 thattracks the amount of fluid collected in gravity container 40 and vacuumcontainers 42 and the amount of fluid pumped by fluid management controlunit 300 and sets off an audible or visual alarm if the differencebetween the amounts of fluid pumped and collected is above a thresholdvalue, thus minimizing the possibility of excess fluid intravasation.

Part of system 10 is a visualizing and imaging assembly 50 that includesa camera 51 coupled to a camera port 106 of hysteroscope 100, and alight source 52 coupled by a fiber optic cable 54 to a light port 109 ofhysteroscope 100. Together, camera 50 and light source 52 allow a userto remotely visualize the tissue at distal end 102 of hysteroscope 100.Assembly 50 also includes an imaging station 70 connected by a fiberoptic cable 56 to camera 50. Imaging station 70 has monitors 72 forviewing images from camera 50 and a capture system 74 for making arecording of the images.

Referring to FIGS. 2A and 2B, hysteroscope 100 includes a sheath 80 thathas a tube 120 with an inner wall 122 defining a channel 121therethrough. Distal end 102 of tube 120 includes a plurality of holes112 in communication with channel 121 for allowing fluid to flow out ofan organ through channel 121. Sheath 80 has a proximal portion 84 thatincludes outflow port 105. Outflow port 105 is in fluid communicationwith channel 121. Positioned between outflow port 105 and channel 121 isan on/off valve 123 for turning on and off fluid flow from channel 121to outflow port 105.

Hysteroscope 100 also includes a scope housing 90 that has an elongatedmember 124 removably receivable in tube 120. Member 124 has an outerwall 126 and an inner wall 125. Inner wall 125 that defines an inflowchannel 130. A proximal portion 94 of scope housing 90 includes inflowport 110, a primary valve 150, and a secondary valve 160, which arefluidly connected to inflow channel 130, as described below. Member 124also defines a lens channel 140 that houses an optical lens 142. Scopehousing 90 has a proximal portion 94 that includes camera port 106 andlight port 109, which are coupled to optical lens 142 by fiber opticlines (not shown). Light travels from light port 109 to distal end 102of hysteroscope 100 to illuminate objects near distal end 102. Images ofthose objects are received by optical lens 142, and travel throughcamera port 106 to camera (FIG. 1), to allow the user to view the organthrough hysteroscope 100. Lens channel 140 is positioned adjacent toinflow channel 130 to help keep optical lens 142 clear of debris duringuse. Proximal portion 94 of scope housing 90 also includes a pin 92receivable in a J-shaped slot (not shown) in sheath 80 to releasablylock scope housing 90 to sheath 80 when member 124 is received in tube120.

Referring also to FIGS. 3A and 3B, when member 124 is received in tube120, inner wall 122 of tube 120 and outer wall 126 of member 124 definea passive outflow channel 128 therebetween. Passive outflow channel 128is divided into a left portion 128A and a right portion 128B, whichreconnect at outflow port 105. Passive outflow channel 128 is in fluidcommunication with holes 112 in distal end 102 of tube 120 and withoutflow port 105 to permit passive outflow of fluid from the organ underthe force of gravity. It will be understood that outflow channel 128need not be divided. Inner wall 125 of member 124 defines inflow channel130 that is in fluid communication with an aperture 108 in distal end102 of hysteroscope 100 to permit fluid flow into the organ. Fluid flowsthrough passive outflow channel 128 along a path that is completelyseparate from a path along which fluid flows through inflow channel 130.

Referring to FIG. 3B, inflow channel 130 and passive outflow channel 128are sized and configured so that fluid management control unit 300,which has an inflow rate of up to 0.7 L/min, is able to maintain asubstantially constant fluid pressure inside a distensible organ bypumping sufficient fluid into the organ through inflow channel 130 tobalance fluid flow out of the organ through passive outflow channel 128,as described below. For example, inflow channel 130 has a D-shapedcross-section with a cross-sectional area, e.g., of about 0.0153 toabout 0.0461 square inches, preferably about 0.0307 square inches, andeach portion 128A, 128B of passive outflow channel 128 has acrescent-shaped cross-section with a combined cross-sectional area,e.g., of about 0.0083 to about 0.0249 square inches, preferably about0.0166 square inches. It should be understood that other configurationsand sizes of inflow channel 130 and passive outflow channel 128 arepossible, so long as outflow of fluid through outflow channel 128 doesnot exceed the ability of fluid management control unit 300 to pumpfluid into the organ through inflow channel 130 at least at the sameflow rate as the outflow of fluid.

Referring to FIGS. 4 and 5, resector 200 includes a stationary elongatedouter tube 202 and a rotatable inner tube 201 that is coupled to workingend 220 (not shown). Inflow channel 130 receives resector 200therethrough. The cross-section of inflow channel 130 enables inflowchannel 130 to be only partially blocked by resector 200, allowing fluidto continue to flow into the organ through a region of inflow channel130 unblocked by resector 200, located between inner wall 125 andelongated tube 202. Inner tube 201 of resector 200 defines a suctionchannel 204 having an opening 206 at working end 220 of resector 200 andin fluid communication with suction port 230 of resector handle 205(FIG. 1) to permit suction of fluid and tissue from the organ. Fluid issuctioned through suction channel 204 along a path that is completelyseparate from the paths along which fluid flows through outflow channel128 and inflow channel 130.

Referring to FIG. 5, passive outflow channel 128, inflow channel 130,and suction channel 204 are sized and configured so that fluidmanagement control unit 300 is able to maintain the substantiallyconstant fluid pressure inside the organ by pumping sufficient fluidinto the organ to balance fluid flow out of the organ through passiveoutflow channel 128 and suction of fluid out of the organ throughsuction channel 204, as described below. For example, the portion ofinflow channel 130 not blocked by resector 200 has a cross-sectionalarea of about 0.0106 square inches, passive outflow channel 128 has across-sectional area of about 0.0166 square inches, and suction channel204 has a cross-sectional area of about 0.0085 square inches. It shouldbe understood that other configurations and sizes of inflow channel 130,passive outflow channel 128, and suction channel 204 are possible, solong as outflow of fluid through outflow channel 128 and suction offluid through suction channel 204 do not exceed the ability of fluidmanagement control unit 300 to pump fluid into the organ through inflowchannel 130 at the same flow rate as the outflow of fluid.

The ability of fluid management control unit 300 to maintain asubstantially constant fluid pressure in the organ is furtherfacilitated by secondary valve 160 of scope housing 90, which maintainssubstantially the same fluid flow impedance through inflow channel 130regardless of whether resector 200 is positioned in scope housing 90.For example, FIG. 14 shows the impedance through hysteroscope 100 atvarious flow rates, regardless of whether resector 200 is positioned inscope housing 90. By maintaining a substantially constant fluid flowimpedance, secondary valve 160 facilitates fluid management control unitmaintaining a substantially constant pressure in the organ regardless ofwhether resector 200 is positioned in scope housing 90. Impedance refersto the pressure drop in fluid between two points (in this case betweeninflow port 110 and the distal end of inflow channel 130) and variesproportional to the square of the flow rate.

Referring to FIGS. 6A and 6B, secondary valve 160 has a housing 162 anda body 164 rotatable within housing 162. Housing 162 includes an inlet167 aligned with inflow port 110 and an outlet 169 aligned with inflowchannel 130. Body 164 defines a throughbore 166 and a smaller diameterblind bore 168 having an open end 168A and a closed end 168B. Blind bore168 intersects throughbore 166 substantially orthogonal to throughbore166 and has a diameter substantially equal to the diameter ofintermediate channel 155.

Body 164 is attached to a handle 165 that allows body 164 to be moveablebetween a first position (FIGS. 6A-6B) defining a first fluid flow pathA and a second position (FIGS. 7A-7B) defining a second fluid flow pathB. When secondary valve 160 is in the first position, blind bore 168 isaligned with outlet 169 and throughbore 166 is parallel to, but offsetfrom, inlet 167 such that body 164 partially blocks inlet 167. Fluidflow along path A is impeded by body 164 partially blocking inlet 167.

Referring to FIGS. 7A and 7B, when secondary valve 160 is in the secondposition, blind bore 168 is aligned with inlet 167 and throughbore 166is aligned with outlet 169 such that fluid can flow through secondaryvalve 160 along path B. In use, with secondary valve 160 in the secondposition, resector 200 is received through throughbore 166 of secondaryvalve 160, such that resector 200 is received within inflow channel 130of hysteroscope 130. Fluid flow along path B is impeded by resector 200partially blocking throughbore 166 and inflow channel 130. The impedanceof fluid flow along path B due to resector 200 blocking fluid flow issubstantially equal to the impedance of fluid flow along path A due tobody 164 blocking fluid flow. Thus, secondary valve 160 allows forsubstantially the same impedance of fluid flow through inflow channel130 and into the organ regardless of whether resector 200 is receivedthrough hysteroscope 100.

Referring also to FIGS. 8A and 8B, a primary valve 150 is positionedbetween inflow port 110 and secondary valve 160 to provide on/offcontrol of fluid flow from inflow port 110 through secondary valve 160into inflow channel 130. Primary valve 150 includes a housing 152 and abody 154 rotatable within housing 152 and defining a throughbore 156.Body 154 is connected to a handle 153 for moving body 154 between afully opened position (FIGS. 6A and 6B), wherein throughbore 156 isaligned with inflow port 110 to allow fluid to flow to inflow channel130, and a fully closed position (FIGS. 8A and 8B), where fluid flow toinflow channel 130 is blocked. Primary valve 150 and secondary valve 160are removably connected to a proximal end 107 of hysteroscope 100 by athreaded portion 161 having a bore 163 therethrough that is aligned withinflow channel 130.

Fluid management control unit 300 maintains a substantially constantfluid pressure inside the organ by pumping sufficient fluid into theorgan through inflow channel 130 to balance fluid flow out of the organthrough passive outflow channel 128 and from suction of fluid throughsuction channel 204 (when resector 200 is received in hysteroscope 100).Referring to FIG. 9, fluid management control unit 300 includesperistaltic pump 310 through which runs fluid line 30 that transmitsfluid from fluid bag 17 to inflow port 110 of hysteroscope 100. Pump 310pumps fluid along fluid line 310, controlling the pressure and flow rateof fluid transmitted to hysteroscope 100.

Fluid management control unit 300 includes a flow rate sensor 315, suchas a roller head, a turbine, or an ultrasonic sensor, that measures theflow rate of fluid outputted by pump 310. Control unit 300 also includesa pressure sensor, e.g., pressure transducer 320, that senses the fluidpressure in fluid line 30 after the fluid passes through pump 310. Fluidmanagement control unit 300 also includes an input 345 where a user caninput a desired pressure to be maintained inside the organ, and a memory340 that contains information on the impedance (i.e., pressure drop)through the hysteroscope 100 and resector 200 combination at a range ofdifferent flow rates.

Coupled to pressure sensor 320, pump 310, flow rate sensor 315, input345, and memory 340, is a controller 330, e.g., a microprocessor, thatcontrols the pressure and the flow rate outputted by pump 310 based onthe flow rate measured by flow rate sensor 315, the pressure measured bypressure sensor 320, the information stored in memory 340, and thetarget pressure 345. Based on a measured flow rate and a measuredpressure, controller 330 determines the actual pressure in the organaccording to the information stored in memory 340 that accounts for theimpedance (i.e., pressure drop) through the hysteroscope 100 at variousflow rates. Controller 330 then compares the pressure in the organ withthe target pressure and adjusts the pressure and flow rate outputted bypump 310 accordingly. If the target pressure is greater than the actualpressure, then controller 330 increases the output of pump 310. If thetarget pressure is less than the actual pressure, then controller 330decreases the output of pump 310.

The size and configuration of inflow channel 130, passive outflowchannel 128, and suction channel 204 facilitate controller 330maintaining substantially constant pressure in the organ. In addition,secondary valve 160 facilitates maintaining a substantially constantpressure in the organ by keeping the impedance through hysteroscope 100the same regardless of whether resector 200 is received in hysteroscope100. Thus, it is not necessary for controller 330 to “know” whetherresector 200 is positioned in hysteroscope 100. Fluid management controlunit 300 is able to maintain a relatively constant pressure of fluidwithin the organ, e.g., at a preset pressure between about 60 mm Hg andabout 120 mm Hg.

Fluid management control unit 300 also includes a feature that verifiesthat a correct combination of hysteroscope 100 and resector 200 is beingused (i.e., to ensure that the system is only used when a resector and ahysteroscope having properly balanced flow channels are attached tofluid management control unit 300). Memory 340 contains flow rate andimpedance information for each valid combination of a hysteroscope and aresector. Controller 330 is programmed to determine whether the pressuremeasured by pressure transducer 320 is within a threshold value of apredetermined pressure for a given flow rate in order to verify theidentity of the combination of the hysteroscope and the resector.Controller 330 is coupled to a shut-off circuit 360 to disable pump 310when controller 330 determines that the combination of hysteroscope andresector is invalid (e.g., when an incorrect size resector is used withthe hysteroscope). If the combination is verified, then controller 330overrides shut-off circuit 360 and allows pump 310 to pump fluid tohysteroscope 100, as described above. On the other hand, if controller330 determines that the combination of the hysteroscope and the resectoris invalid (e.g., wrong size resector), the controller 330 activatesshut-off circuit 360 to disable pump 310. Controller 330 also is coupledto an alarm 350, e.g., a visual or audible alarm, that is activated whenpump 310 is disabled. Controller 330 is programmed to make pressurecomparisons at several (e.g., three or four) flow rates prior to use ofhysteroscope 100 and resector 200.

In use, a user assembles the components of resection system 10 as shownin FIG. 1. As shown in FIGS. 7A and 7B, the user positions primary valve150 in the open position and secondary valve 160 in the second position.The user inserts resector 200 through hysteroscope 100. The userverifies the combination of hysteroscope 100 and resector 200 byactivating fluid management control unit 300, as described above withrespect to FIG. 9, to infuse fluid through hysteroscope 100 and resector200 assembly at three or four different flow rates, to sense the flowimpedance through the assembly, and to compare each sensed flowimpedance to predetermined flow impedances. If the combination isverified, the user removes resector 200 from hysteroscope 100, closesprimary valve 150, and moves secondary valve 160 to the first position,as shown in FIGS. 8A and 8B.

Referring to FIG. 10, to position sheath 80 within the uterus, system 10includes an obturator 800 insertable through sheath 80 when scopehousing 90 is removed from sheath 80. Obturator 800 includes a shaft810, a sharp, distal tip 820, and a proximal handle 840. Disposedbetween handle 840 and shaft 810 is a pin 830 that fits into theJ-shaped slot (not shown) in sheath 80 to removably lock obturator 800to sheath 80.

Referring to FIG. 11, with obturator 800 received within sheath 80 suchthat tip 820 extends beyond distal portion 102 of sheath 80, the userinserts obturator 800 and sheath 80 into a uterus 900. Referring to FIG.12, the user removes obturator 800 from sheath 80, and inserts scopehousing 90 through sheath 80 and into uterus 900. The user then opensprimary valve 150 while leaving secondary valve 160 in the firstposition, as shown in FIGS. 6A and 6B, and activates fluid managementcontrol system 300 to pump fluid through channel 130 of hysteroscope 100and into uterus 900 along flow path A, at a first impedance, to distenduterus 900, as shown in FIG. 12. At the same time, the user allows fluidto flow out of uterus 900 via holes 112 and channel 122 in hysteroscope100 along flow path C to gravity container 40, in order to keep thepressure inside uterus 900 between about 60 mm Hg and 120 mm Hg.

Once uterus 900 has been distended, with primary valve 150 still open,the user positions secondary valve 160 in the second position, as shownin FIGS. 7A and 7B, and inserts resector 200 through secondary valve 160and inflow channel 130 of hysteroscope 100, and into uterus 900, asshown in FIG. 13. Fluid management control system 300 continues to pumpfluid so that fluid flows through inflow channel 130, between inner wall125 and resector 200 and into uterus 900 at a second impedancesubstantially equal to the first impedance. At the same time, the userallows fluid to flow out of uterus 900 via holes 112 and channel 128 inhysteroscope along flow path C and suctions fluid out of uterus 900through resector 200 along flow path D, in order to keep the pressureinside uterus 900 between about 60 mm Hg and 120 mm Hg. Fluid suctionedalong path D is collected in vacuum containers 42. The user also canactuate vacuum regulator 400 to control the amount of suction throughresector 200 along path D. Preferably, the user maintains the vacuumpressure above approximately 100 mm Hg (to facilitate tissue removal)and below approximately 200 mm Hg (to inhibit uterus collapse). In orderto inhibit uterus collapse, vacuum regulator 400 is preset to not allowvacuum pressure greater than a threshold value, e.g., 200 mm Hg, to beapplied.

The user visualizes the inside of uterus 900 on monitors 62 ofvisualizing and imaging assembly 50. The user actuates foot pedal 62,which activates resector control unit 60. Resector control unit 60activates resector 200, e.g., by rotating a cutting blade 910 at workingend 220 of resector 200, to cut tissue from uterus 900. Fluid and tissuecut by blade 910 are suctioned through channel 204 of resector 200 alongpath D. During the procedure, resector 200 can be removed fromhysteroscope 100 while hysteroscope 100 remains inside uterus 900, e.g.,to clean resector 200 or change instruments, so long as the user movessecondary valve 160 to the closed position, as shown in FIGS. 6A and 6B,while removing resector 200 to permit greater inflow through channel 130of hysteroscope 100.

During the procedure fluid monitor unit 18 tracks the amount of fluidinfused through resector 200 and the amount of fluid collected ingravity container 40 and vacuum containers 42. Fluid monitor unit 18sets off an audible or a visual alarm if substantially more fluid isinfused than collected, which indicates that the patient is absorbingtoo much fluid. Once the procedure is complete, the user closes primaryvalve 150, as shown in FIGS. 8A and 8B, and removes resector 200 andhysteroscope 100 from uterus 900.

A number of embodiments of the invention have been described.Nevertheless, it will be understood that various modifications may bemade without departing from the spirit and scope of the invention. Forexample, the shape, size, and configuration of the fluid flow channelsthrough the hysteroscope and the resector could be different than thatshown and described, such as having an inflow channel with anelliptical, square, triangular, or trapezoidal cross-section. Instead ofa blind bore, the body of the secondary valve could include a peripheralchannel formed in an outer surface of the body. Instead of a secondaryvalve, the primary valve could be electronically controlled to maintaina constant impedance through the hysteroscope regardless of whether theresector is inserted through the hysteroscope. The hysteroscope can beused with other types of resector tools having rotatable working ends,such as burrs or drills. The hysteroscope also can be used with aresector tool having a reciprocating working end, such as the instrumentdisclosed in U.S. patent application Ser. No. 10/318,400 entitled“Reciprocating rotary arthroscopic surgical instrument,” the entirety ofwhich is incorporated herein by reference. The fluid management systemcan include another type of pump, such as a centrifugal, piston, ordiaphragm pump. The vacuum regulator could include a manually orelectronically operable valve, a flow sensor, and/or a pressure gauge.The devices shown can be used for surgery on other distensible organs,such as a shoulder or knee joint. Different combinations of thecomponents of the system could be used or components could be added ordeleted. These and other embodiments are within the scope of thefollowing claims.

What is claimed is:
 1. An endoscope comprising: an elongated memberdefining an inflow channel and being configured to accept an instrumentinserted therethrough and be inserted into a patient; and a valveassembly coupled to a proximal end of the elongated member andincluding: (i) a valve housing having a resector inlet, a valve inlet influid communication with a fluid source, and a valve outlet coupled tothe elongated member and in fluid communication with the inflow channel,and (ii) a valve body rotatable within the valve housing between thevalve inlet and the valve outlet to regulate an impedance of fluid flowthrough the endoscope, the valve body defining a throughbore and a blindbore that is perpendicular to and in fluid communication with thethroughbore, wherein, in a first position of the valve body, thethroughbore is aligned with the valve inlet and the blind bore isaligned with the valve outlet, and, in a second position of the valvebody, the throughbore is aligned with the valve outlet and resectorinlet, and the blind bore is aligned with the valve inlet, and wherein afirst impedance of fluid flow through the valve housing with the valvebody in the first position is substantially equal to a second impedanceof fluid flow through the valve housing with the valve body in thesecond position and with a resector extending into the resector inlet,through the throughbore, and into the inflow channel of the elongatedmember.
 2. The endoscope of claim 1, wherein the valve assembly furtherincludes a second valve including: (i) a second valve housing having asecond valve inlet configured to receive fluid from the fluid source anda second valve outlet configured to flow fluid to the valve inlet of thevalve, and (ii) a second valve body rotatable within the second valvehousing between the second valve inlet and the second valve outlet toprovide ON/OFF fluid control for the endoscope, and a diameter of theresector inlet is smaller than a diameter of the throughbore.
 3. Anendoscope comprising: an elongated member including an inner walldefining an inflow channel and being configured to be inserted into apatient and accept an instrument inserted therethrough; and a valveassembly in fluid communication with the inflow channel and including avalve housing and a valve body, the valve housing including a valveinlet coupled to a fluid inlet line and a valve outlet coupled to aproximal end of the elongated member, and the valve body being withinthe valve housing between the valve inlet and the valve outlet and beingrotatable to selectively define a first fluid path and a second fluidpath through the endoscope, wherein an impedance of fluid flow throughthe endoscope without the instrument inserted therethrough and with thevalve body defining the first fluid path is substantially equal to animpedance of fluid flow through the endoscope with the instrumentinserted therethrough and with the valve body defining the second fluidpath.
 4. The endoscope of claim 3, wherein the valve body in a firstposition partially defines the first fluid path, and the valve body in asecond position partially defines the second fluid path.
 5. Theendoscope of claim 4, wherein the valve body is rotated 90 degreesbetween the first position and the second position.
 6. The endoscope ofclaim 3, wherein the valve body defines an angled bore.